Optical designs of electronic contact lens to decrease myopia progression

ABSTRACT

A soft contact lens comprises a plurality of light sources coupled to a plurality of optical elements. The plurality of light sources and the plurality of optical elements are embedded in a soft contact lens material. Each of said plurality of optical elements generates an image focused in front of a peripheral retina of a wearer. In some embodiments, each of the images is focused at a distance in front of the peripheral retina at a location, and each of the images comprises a depth of focus and a spatial resolution. The depth of focus can be less than the distance, and the spatial resolution greater than a spatial resolution of the peripheral retina at the location.

RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 17/250,507, filed Jan. 29, 2021, which is a 371 national phase of PCT/US2019/043692, filed Jul. 26, 2019, published as WO 2020/028177 on Feb. 6, 2020, and claims the benefit under 35 U.S.C. § 119(e) of U.S. Provisional Patent Application No. 62/711,909, filed Jul. 30, 2018, and of U.S. Provisional Patent Application No. 62/843,426, filed May 4, 2019, the disclosures of which are incorporated, in their entirety, by this reference.

BACKGROUND

Myopia, or near-sightedness, is a refractive error in which far objects are focused anterior to the retina. This can be related to the axial length of the eye. In general, a 1.0 mm increase in axial length of the eye corresponds to an increase in myopia of 2.5 Diopters (“D”).

Spectacle lenses, contact lenses and refractive surgery can be used to treat refractive errors of the eye such as myopia. Although these approaches can be effective in treating myopia, the eye may continue to grow axially, such that the amount of myopia continues to increase. The relatively high prevalence of myopia has prompted studies to understand the underlying mechanisms of axial growth and the development of possible treatment directed to axial growth.

While myopia is known to have genetic causes, the dramatic increase in the incidence of myopia cannot be explained by genetic factors alone; rather, they must be interpreted simply as the remarkable ability of the visual system to adapt to altered environmental conditions, specifically a shift in visual habits from long to short distances and from open to enclosed spaces.

Although pharmaceutical treatments have been proposed to treat myopia associated with axial length growth, these treatments can have less than ideal results in at least some instances. While atropine and other muscarinic agents can slow myopia progression, possible concerns about post treatment rebound effects and the short and long-term side effects associated with prolonged treatment may have discouraged the widespread use of these drugs.

Some studies suggest a role for retinal defocus in myopia progression. Animal studies have demonstrated that refractive development and axial growth can be regulated by visual feedback associated with the eye's effective refractive status. Work in relation to the present disclosure suggests that visual signals in the periphery of the retina can influence ocular shape and axial length in a manner that is independent of central vision.

Work in relation to the present disclosure suggests that the retinal shell becomes more aspheric as the eye becomes more myopic. Examples of image shells on the retina with myopic eyes and traditional correction are described in Cooper, J, “A Review of Current Concepts of the Etiology and Treatment of Myopia” in Eye & Contact Lens, 2018; 44: pp 231. With traditional spherical lenses, the peripheral aspheric retina of the myopic eye receives light focused behind the retina while light is focused at the center of the retina, which can trigger a growth signal because the peripheral light is focused behind the retina, similarly to an eye with insufficient axial length. A conventional spherical or toric lens (e.g. a contact lens or a spectacle lens) generally cannot generate an image shell that matches the optimum shape required for refractive correction that would stop the growth signal to the retina to become even more myopic. One approach has been to provide an aspheric lens that focuses light onto the peripheral regions of the aspheric retina.

Previous refractive correction devices to prevent myopia progression may produce less than ideal results in at least some instances. The refractive correction to provide appropriate focus at the peripheral retina can require a highly aspheric image shell, that can be created by a highly aspheric optic. Unfortunately, such an aspheric optic can generate a central image with a substantial aberration, compromising far vision and reducing quality of vision of the wearer in at least some instances. One approach has been to limit the amount of asphericity to about 2 D or less in order to provide distance vision without significant aberrations to central vision, but this limitation on the amount of asphericity can also limit the amount of correction to peripheral portions of the retina, which can lead to a less than ideal treatment in some instances.

Studies in animal models as well as clinical studies have suggested that the retina can distinguish a “plus blur” from a “minus blur”, or image blur caused by a myopic defocus from a hyperopic defocus, possibly by utilizing longitudinal chromatic aberration as a guide, since the sign of the longitudinal chromatic aberration will be opposite, depending on whether the image blur is hyperopic or myopic. However, prior clinical approaches may not have not adequately addressed chromatic aberration to decrease myopia progression in at least some instances.

Therefore, a new approach is needed to decrease myopia progression that can meet the expectation of comfort and performance by young wearers while providing an effective peripheral hyperopic defocus.

SUMMARY

In some embodiments, a contact lens comprises a light source 30 and optics to form an image in front of the retina with one or more of an appropriate resolution, depth of focus or diffraction. The image formed in front of a region of the retina may comprise a resolution finer than the resolution of the retina at the region. The light beam can be directed to the region of the retina at an angle relative to the optical axis of the eye, so as to illuminate an outer portion of the retina with a resolution finer than the corresponding location of the retina. The depth of focus can be configured to illuminate the retina with an appropriate amount of blurring of the image on the retina, and the diffraction of the spot can be appropriately sized to provide resolution of the image formed in front of the retina finer than the resolution of the retina.

In accordance with some embodiments, a soft contact lens comprises micro-displays located away from a center of the contact lens and toward a periphery of the contact lens, in which each of the micro-displays is coupled to a micro-lens array located posteriorly to the micro-display. The micro-displays may comprise an OLED (organic light emitting diode) or an array of micro-LEDs. The micro-lens arrays can be optically coupled with the displays to efficiently collect light from the micro-displays, and collimate the light and/or converge the light before projecting the light into the entrance pupil. The virtual images created by these displays can be myopically defocused and placed symmetrically in a plurality of regions on the retina, such as four sectors (nasal-inferior, nasal-superior, temporal-inferior and temporal-superior). The micro displays can be located away from the optical center of the lens by a distance within a range from 1.5 mm to 4.0 mm, such as 2.5 mm to 3.5 mm. The central optical zone 14 of the contact lens can be configured to provide emmetropic vision for the wear, and may have a diameter within a range 3.0 to 5.0 mm. Each micro-display can generate a retinal image with an appropriate shape, such as circular or arcuate and at an angle of about 20-60 degrees at the fovea. In some embodiments, the retinal images are formed at the peripheral retina at an eccentricity in the range of 15 degrees to 40 degrees, for example within a range from 20 to 30 degrees. The contact lens may comprise an electronic control system mounted with the micro-displays on a flexible transparent sheet of material such as plastic and other components.

In some embodiments, the micro displays 12 may comprise OLEDs with pixel sizes within a range from 2.0 micrometers (microns) to 5.0 microns, with a pitch in the range of 2.0-10.0 microns. In some embodiments, the micro-displays embedded in the contact lens comprise micro-LEDS illuminating an object, such as a thin film placed in front of it and toward the eye. The micro-displays may comprise polychromatic or monochromatic micro-displays. The polychromatic images can be formed by RGB pixels in the OLED or micro-LEDS of different colors, organized in arrays so as to form an RGB display. In some embodiments, the wavelength for stimulation of change in axial length is within a range from about 450 nm to about 560 nm, and can be near 500 nm, the peak wavelength of stimulation of rods in the eye, although other wavelengths may be used.

In some embodiments, an optical configuration comprises one or more light sources coupled to a light processing structure that comprises one or more of collimating lenses, mirrors, lightguides, waveguides, or holographic mirrors. The light processing structure images the one or more light sources so as to a project an image of the light source in front of the peripheral retina, such that the focus of the image is in front of the retinal surface. In some embodiments, the optic configuration is placed at or near the anterior surface of the contact lens, and rays from the micro-displays are focused by the contact lens. The contact lens can be configured to provide refractive correction to the wearer, and the display optics configured to provide additional focus to provide the defocused image of the micro-display on the retina. In some embodiments, the amount defocus is in within a range from about 2.00 Diopter (D) to 6.00 D, and can be within a range from about 2.0 D to 4.0 D.

BRIEF DESCRIPTION OF THE DRAWINGS

A better understanding of the features, advantages and principles of the present disclosure will be obtained by reference to the following detailed description that sets forth illustrative embodiments, and the accompanying drawings of which:

FIG. 1 shows a soft contact lens, in accordance with some embodiments;

FIG. 2A shows OLED micro displays mounted on the inner surface of soft contact lens, optically coupled with micro lens arrays for projecting images with myopic defocus on the periphery of the retina of a wearer, in accordance with some embodiments;

FIG. 2B shows a soft contact lens comprising a plurality of light sources and optics and associated circuitry, in accordance with some embodiments;

FIG. 2C shows mechanical integration of the function of the components of the contact lens as in FIG. 2B;

FIG. 3 shows an optical configuration in which the optical path length is increased by folding back the optical path using two mirrors, in accordance with some embodiments;

FIG. 4 shows a ray tracing simulation of the optical configuration shown in FIG. 3, in which the Liu Brennan eye model has been used to compute the retinal image, in accordance with some embodiments;

FIGS. 5A and 5B show analysis of retinal image quality generated by the optic configuration of FIG. 3;

FIG. 6 shows analysis of depth of focus of the optic configuration shown in FIG. 3;

FIG. 7 shows the MTF for the analysis of FIG. 6.

FIGS. 8A and 8B show an optical configuration comprising a lens to focus light onto the retina, in accordance with some embodiments;

FIG. 9 shows analysis of retinal image quality generated by the optic configuration shown in FIGS. 8 and 8B, in accordance with some embodiments;

FIG. 10 shows analysis of depth of focus of the optic configuration shown in FIGS. 8A and 8B.

FIGS. 11A and 11B show a light-pipe in order to increase the optical path length, in accordance with some embodiments;

FIG. 12 shows soft contact lens with embedded light sources, optics and electronics, in accordance with some embodiments;

FIG. 13 shows a ray tracing simulation of the peripheral retinal image formed by a combination of a microscopic light source and a micro-optic, in accordance with some embodiments;

FIG. 14 shows four object points used to simulate image quality using ray tracing for a light source comprising four simulated object points, in accordance with some embodiments;

FIG. 15 shows the quality of a peripheral image generated by a reflective optic, in which Modulation transfer functions (MTF) of all the object points are substantially coincident, in accordance with some embodiments;

FIG. 16 shows depth of focus of the peripheral image formed by the reflective optic, in accordance with some embodiments;

FIG. 17 shows the effect of myopic blur on image resolution of the peripheral retinal image formed by the reflective optic, as measured by change of the magnitude of MTF at a single spatial frequency (20/200 or 10 line pair per mm “lp/mm” or 10 arc min) as a function of the magnitude of myopic defocus for the reflective optical design, in accordance with some embodiments;

FIG. 18 shows MTF plots of the retinal image formed by the refractive optic for the four object points shown in FIG. 14, in accordance with some embodiments;

FIG. 19 shows depth of focus of the image formed by the refractive optic, in accordance with some embodiments;

FIG. 20 shows MTF computed for a single spatial frequency (20/200 or 10 lp/mm, or 10 arc min) as a function of myopic defocus, in accordance with some embodiments;

FIG. 21 shows MTF plots of the four object points in FIG. 14 for embodiments comprising a miniature lightguide, in which a substantial difference in image quality exists between sagittal and tangential planes, indicating non-symmetrical aberrations, in accordance with some embodiments;

FIG. 22. Depth of focus of the peripheral retinal image projected by the lightguide optic, in accordance with some embodiments;

FIG. 23 shows MTF plots at a single spatial frequency (20/200) plotted against the magnitude of myopic defocus of the peripheral image on the retina for embodiments with light guides;

FIG. 24 shows a comparison of depths of focus of the peripheral images generated by the three projection systems, comprising a refractive optic, a reflective optic and a lightguide optic, in accordance with some embodiments;

FIG. 25 shows depth of focus of the retinal image generated by a reflective optic design, in accordance with some embodiments and

FIG. 26 shows MTF values at a single spatial frequency plotted against magnitude of myopic defocus for the peripheral image created by the reflective optic design of FIG. 25, in accordance with some embodiments.

DETAILED DESCRIPTION

In accordance with some embodiments, a soft contact lens comprises peripheral micro-displays, each of which is fronted eye side by a micro-lens array. The micro-displays may comprise an OLED (organic light emitting diode) or an array of micro-LEDs. Light emitted by these displays is typically Lambertian. The micro-lens arrays are optically coupled with the displays, so that they can efficiently extract light from the micro-displays, collimate the light and focus it before projecting them into the entrance pupil. The virtual images created by these displays will be myopically defocused and will be placed symmetrically in the four sectors (nasal-inferior, nasal-superior, temporal-inferior and temporal-superior), in some embodiments. The micro displays will be located away from the optical center of the lens by a distance within a range from 1.5 mm to 4.0 mm, preferably 2.5 mm to 3.5 mm, in some embodiments. The central optic of the contact lens can be selected to bring the wearer as close to emmetropia as possible, and may have a diameter within a range 3.0 to 5.0 mm. Each micro-display will be circular, rectangular or arcuate in shape and will each have an area within a range from 0.01 mm² to 8.0 mm², for example within a range from 0.04 mm² to 8.0 mm², for example within a range from 1 mm² to 8 mm², or preferably within a range from 1.0 mm² to 4.0 mm², in some embodiments. In some embodiments, each of the plurality of micro-displays comprises the light source, the back plane and associated electronics with the dimensions and shapes as described herein. The contact lens will have an electronic control system as well as the micro-displays mounted on a flexible transparent sheet of plastic. The electronic system may comprise an ASIC or a microcontroller, a rechargeable Lithium ion solid state battery, a voltage ramping module e.g., a buck boost converter, a flash memory and an EEPROM, an RFID module to provide wireless recharging, or an antenna preferably disposed radially along the edge of the contact lens, and any combination thereof. The contact lens comprises a biocompatible material, such as a soft hydrogel or silicone hydrogel material, and may comprise any material composition that has proven to be compatible with sustained wear on the eye as a contact lens.

In some embodiments, virtual images focused at a target distance from the peripheral retina, equivalent to a myopic defocus. Rays forming these images do not come from outside environment but from the micro-displays themselves, so the optics of the micro-lens arrays can be solely designed to process the rays emanating from the micro-displays. The area of each of these micro-displays and micro-lens arrays in front of each is small, so the obscuration of the real image is small, as shown in FIGS. 1 and 2.

The device as described herein can give each caregiver substantial flexibility in setting and testing such parameters for an individual patient, then refining the preferred parameters of treatment based on observations of patient response.

Some embodiments comprise a contact lens of diameter 14.0 mm, with an edge zone of 1.0 mm and a peripheral zone 16 whose inner diameter is 6.0 mm and outer diameter is 12.0 mm. The overall diameter of the lens may be in the range of 13.0 mm and 14.5 mm, preferably 13.5 and 14.5 mm. The central optical zone 14 is designed to cover the pupil of all wearers under all illumination conditions, and should therefore have a diameter in the range of 5.0 mm and 8.0 mm. The peripheral or the blend zone is primarily designed to provide a good fit to the cornea, including good centration and minimum decentration. The central optical zone 14 is designed to provide emmetropic correction to the wearer and may be provided with both spherical and astigmatic correction (FIG. 1). Contact lens designs suitable for incorporation in accordance with embodiments disclosed herein are described in Douthwaite, D. A., “Contact lens optics and lens design”, 3^(rd) edition, 2006; ISBN 978-0-7506-88-79-6; Butterworth-Heinemann.

In some embodiments, the inner surface of the contact lens is embedded with a set of four micro-displays coupled eye side with micro-lens arrays of the same size. The function of the micro-lens arrays is to collimate the light being emitted by the micro-displays, collimate it, and focus it at a focus that is designed to be in the front of the eye, to provide hyperopic defocus. The micro-displays can be sized in many ways, and each of these micro-displays is only about 0.04 mm² to 2 mm² in area, for example from 1 mm² to 2 mm² in area, so that these displays cover less than 1% of the contact lens optic, in some embodiments. Each of the displays will generate about 30-50 cd/m² or greater of illumination, quite sufficient for forming a relatively bright image at the focus of each of these micro-displays. The focused images will appear approximately 1.5-2.5 mm in front of the peripheral retina, since they will be designed to be myopic by about 2.0 D to 5.0 D, for example 2.0 D to 4.0 D, or preferably 2.5 D to 3.5 D, for example.

In some embodiments, the micro displays may be OLEDs with pixel size of 2.05.0 microns, with a pitch in the range of 2.0-10.0 microns. In some embodiments, the micro-displays embedded in the contact lens as described herein will consist of micro-LEDS illuminating an object, such as a thin film placed in front of it, eye side. The micro-displays may be polychromatic or they may be monochromatic. The polychromatic images are formed by RGB pixels in the OLED or micro-LEDS of different colors, organized in arrays so as to form an RGB display. Data on wavelength dependence of axial length alteration of the projected hyperopic or myopic image at the peripheral retina are lacking. A preferred wavelength for stimulation of change in axial length is 500 nm, the peak wavelength of stimulation of rods in the eye, although other wavelengths may be used.

The amounts and location of illumination on outer locations of the retina to provide a therapeutic benefit can be determined by one of ordinary skill in the art without undue experimentation in accordance with the teachings disclosed herein. The length and duration of peripheral stimulation can be determined, for example optimized, based on available preclinical data in animal models. For example, some studies suggest that changes in axial length in animal models can be obtained on repeated application of defocus stimuli, in preference to a single sustained period of equivalent duration of imposed defocus. Examples of studies with information on illumination changes in axial length suitable for incorporation in accordance with the embodiments disclosed herein include: Wallman, J., et al, “Homeostatis of eye growth and the question of myopia”, in Neuron, 2004; 43: pp 447; Benavente-Perez, A, et al, “Axial Eye Growth and Refractive Error Development Can Be Modified by Exposing the Peripheral Retina to Relative Myopic or Hyperopic Defocus” In IOVS 2014; 55: pp 6767; and Hammond, D. S., et al, “Dynamics of active emmetropisation in young chicks—influence of sign and magnitude of imposed defocus” in Ophthalmic Physiol Opt. 2013; 33: pp 215-222.

Work in relation to the present disclosure suggests that the duration and distribution of application of peripheral myopic defocus will depend on individual physiology and the precise shape of the retina. An embodiment comprises a reprogrammable MCU or ASIC controlling the operation of the micro-displays, and a real time clock that will enable adjustment of the treatment duration and periodicity by the caregiver, throughout the treatment. This embodiment also enables the caregiver to test whether nocturnal stimulation (sustained or repeated sequence of short pulses) has an efficacy for certain individuals.

In some embodiments, the electronic components are populated on a flexible thin film on which interconnects and electrical bus are deposited by means of vapor deposition or a 3D printing process. In some embodiments, the electronics and the micro-displays are further coated with a flexible stack of thin barrier film, such as a stack of Paralyne C and SiO_(x) film of total thickness 5-10 microns, developed by Coat-X, a corporation located in Neuchatel, Switzerland.

Some embodiments of the device deploy a set of one to eight micro-displays, each circular or arcuate in shape, and they are disposed radially on the inner surface of the contact lens, all at the same distance from the optical center of the lens. In one embodiment, they may be monochromatic. In another embodiment they may be designed to provide white light output. In a third embodiment, they may be designed to output illumination matched to the retinal sensitivity. These micro-displays are operated and controlled by a reprogrammable microcontroller (MCU) or an ASIC.

In some embodiments, the contact lens is worn during sleep, and the micro-displays are programmed to operate only when the wearer is asleep. Such a programmed stimulation of reduction of the axial length will interfere minimally with daily activities, including reading and computer work. The contact lens may even be removed during daytime activities, while it is fit on the cornea just before going to sleep. Other embodiments may utilize other programming algorithms, for example a combination of daytime and nighttime stimulations.

In some embodiments, the contact lens may be a daily disposable lens, obviating the need for disinfecting and cleaning the lens or recharging it. Another embodiment consists of a contact lens of planned replacement modality.

In some embodiments, each micro-display (1 mm² to 4 mm²) will consume about 10 microwatts of electrical energy. In these embodiments, a set of four micro-displays may use about 125 microwatt-hours of electricity for 2 hours of operation, so that the total daily energy consumption for this design will be expected to be 0.2 milliwatt-hour. In some embodiments, each micro-display comprises a cross-sectional area within a range from about 0.04 mm² to 4 mm² and consumes about 10 microwatts of electrical energy. In some embodiments, the electrical power is supplied by a rechargeable, solid state lithium ion battery. A bare die solid state rechargeable lithium ion battery, marketed by Cymbet Corporation, may be populated on the same flexible substrate as the electronics of the lens. For example, a 50 uAH rechargeable lithium ion solid film battery has dimensions of 5.7×6.1 mm×0.200 mm (Cymbet Corporation CBC050). In some embodiments, the battery comprises sufficient mass to stabilize the contact lens. For example, the battery can be located on an inferior position of the lens in order to stabilize the lens with gravity. The inferiorly located battery may comprise a mass sufficient to decrease rotational movement such as spinning when the wearer blinks.

In some embodiments, an electronic contact lens projects a 2.0-5.0 D myopically defocused image at the retinal periphery, while maintaining excellent vision at the center.

In some embodiments, the electronic soft contact lens comprises microscopic light sources and microscale optics embedded at the periphery of the lens optic. The contact lens optic can be designed to provide excellent vision at the central retina, while the outer light sources project images at the outer portions of the retina that are myopically defocused. In some embodiments, the light sources comprise micro displays. In some embodiments, the outer images formed anterior to the retina may to stimulate the retina to move forward, reducing the axial length and deepening the vitreous compartment. In some embodiments the contact lens is configured to one or more of decrease myopia progression, substantially stop myopia progression, or reverse myopia in the eye wearing the lens. In some embodiments, the contact lens can be configured for extended wear and replaced once a month, for example. The contact lens can be replaced more frequently or less frequently, for example, once a week, or once every three months. In some embodiments, the contact lens is designed to be worn by teens and young adults, who can be at greater risk of myopia progression than people of other ages.

In some embodiments, the amount of myopic defocus of the peripheral image is within a range from about 2.0 D to about 5.0 D, for example from about 2.5 D to about 5 D. Based on the teachings disclosed herein a person of ordinary skill in the art can conduct studies such as clinical studies to determine appropriate amounts of defocus, illumination intensities and times of illumination. In some embodiments, one or more of the amount of defocus, the retinal locations of the retinal illumination or the times of illumination can be customized to an individual, for example in response to physiological characteristics of the individual patient. The duration of treatment can be within a range from 1 to 3 years, for example about 2 years. In some embodiments, the treatment is performed with a number of lenses within a range from about 10 lenses to about 40 lenses, for example from about 10 lenses to about 30 lenses. The prescription of the optical zone 14 comprising the central lens optic may change with time during treatment, and the prescription of the contact lens can be changed is appropriate. The contact lenses as disclosed herein may also be subsequently worn as needed, for example if myopia progression returns.

The electronic contact lens can be configured in many ways to correct refractive error of the wearer. In some embodiments, the contact lens comprises a plurality of micro-displays that emit light near a periphery of the optical zone 14 of the contact lens, a plurality of micro-optics to collect, collimate and focus the light rays emanating from the light sources, a miniaturized rechargeable solid state battery to provide power to the light sources (e.g. a Lithium ion solid state battery), an antenna to wirelessly receive power to recharge the battery, and a micro-controller to control actuating and controlling functions, and a memory to store data or software instructions.

In some embodiments, the outer image comprises a peripheral image located outside the macula, for example within a range from about 20 degrees to about 30 degrees eccentric to the fovea.

The contact lens can be configured in many ways with a plurality of optics such as micro-optics to collect light from a plurality of light sources (e.g. microscope light sources) and form an image anterior to an outer portion of the retina such as anterior to a peripheral portion of the retina. In some embodiments, the plurality of optics comprises one or more of a light-pipe and a reflective component, such as mirrors, for example microscopic mirrors.

The device as described herein can be used to treat advancement of refractive error such as myopia. In some embodiments, each caregiver has substantial flexibility in setting and testing parameters for an individual patient, then refining the preferred parameters of treatment based on observations of patient response.

In some embodiments, the optical design of the refractive properties of the contact lens substantially unaltered and can be configured in many ways. For example, the central optical zone 14 of the contact lens can be optimized for best correction of the far image at the fovea, while providing images at the periphery of the retina that are anterior to the image shell of the contact lens optic, so as to decrease the advancement of refractive error. In some embodiments, the light sources may comprise a surface area of no more than 2 mm² of the optical surface, and the size of the optical surface to correct refractive error can be within a range from about 25 mm² to about 50 mm², which can decrease the effect of the light source on vision. An intensity of the peripheral image that can be provided independently of the level of ambient illumination, and the intensity of the light sources can be adjusted over several orders of magnitude by selecting light sources of appropriate power. The soft contact lens can be configured to provide appropriate amounts of illumination response to input from the wearer or a health care provider.

FIG. 1 shows micro-displays 12 embedded in the contact lens 10. The soft contact lens 10 comprises an optical zone 14 configured to provide far vision correction to the wearer, for example with a visual acuity of 20/20 or better. The micro-displays 12 can be configured to provide the images in front of the peripheral portion of the retina as described herein. This configuration can allow the user to have good visual acuity while receiving therapy from the images focused in front of the retina as described herein.

The micro-displays 12 may comprise micro-LEDS illuminating an object, such as a thin film placed in front of it, eye side. The light emitted by these micro-displays 12 can be Lambertian and directed to an optical element such as a lens to direct the light beam toward the retina. The contact lens 10 comprises a diameter suitable for placement on an eye. For example, the contact lens 10 may comprise a diameter within a range from about 10 mm to 15 mm, for example 14.0 mm. The contact lens 10 may comprise a plurality of embedded micro-displays 12. Each of the plurality of micro-display 12 can be optically coupled to an optical configuration that collects light emitted by the micro-display 12 and projects an image on or in front of the retina of the wearer at a specified eccentricity. Each of the displays 12 can generate an illumination within a range from about 1 cd/m² to about 50 cd/m². The amount of illumination can be sufficient for forming a relatively bright image at the focus of each of these micro-displays 12.

In some embodiments, the amount of illuminance is intermediate between photopic and mesopic levels of illumination and intermediate levels of sensitivity of rods and cones. The preferred amount of illumination can be within a range from about 0.1 cd/m² to about 10 cd/m², preferably between 0.5 cd/m² to 5 cd/m² at the pupil plane. This amount of illuminance may correspond to an amount of light between moonlight and indoor lighting, for example. In some embodiments, the amount of illumination corresponds to mesopic vision.

In some embodiments, the micro-displays 12 can comprise light sources that emit polychromatic light composed of light of different wavelengths. In other embodiments, the light sources emit monochromatic light. In some embodiments, the wavelength of the monochromatic illumination can be in the range of 500 nm to 560 nm, preferably from 500 nm to 530 nm, more preferably from 500 nm to 510 nm.

In some embodiments, the polychromatic light sources provide chromatic cues to the peripheral retina. The chromatic cues may comprise negative chromatic aberration. In some embodiments, a poly chromatic light beam is focused anterior to the retina, in which the polychromatic light beam comprises a positive chromatic aberration prior to an image plane 35 or a focal plane and a negative chromatic aberration after the image plane 35 or focal plane so as to illuminate the retina with a negative chromatic aberration.

While the polychromatic illumination can be configured in many ways, in some embodiments, the polychromatic illumination comprises red illumination, blue illumination and green illumination, although other wavelengths of light may be used.

In some embodiments, the projected images appear approximately 1.5 mm to about 2.5 mm in front of the peripheral retina, since they will be designed to be myopic by about 2.0 D to 4.0 D, preferably 2.5 D to 3.5 D. In general, 1 mm in front of the retina corresponds to about 2.5 D of myopia, for example about 2.7 D of myopia.

This approach of peripheral stimulation of change in axial length through thickening or thinning of the choroid can be based on repeated and confirmed observations of the efficacy of application localized hyperopic or myopic defocus in stimulating change in the axial length of the eye 11. The length and duration of peripheral stimulation can be based on available preclinical data in animal models as is known to one of ordinary skill in the art. For example, the rate of change in axial length can obtained on repeated application of defocus stimuli, in preference to a single sustained period of equivalent duration of imposed defocus.

In some embodiments, the duration and distribution of application of peripheral myopic defocus depends on individual physiology and the shape of the retina. In some embodiments, the contact lens 10 comprises a programmable processor such as a microcontroller unit (MCU) or application specific integrated circuitry (ASIC) for controlling the operation of the micro-displays 12. The contact lens 10 may comprise a real time clock to adjust the treatment duration and periodicity by the caregiver, and the treatment duration and periodicity may be provided throughout the treatment. In some embodiments, the caregiver tests whether nocturnal stimulation (sustained or repeated sequence of short pulses) has an efficacy for certain individuals.

FIG. 2A shows OLED micro displays 12 mounted on the inner surface of soft contact lens 10, optically coupled with micro lens arrays for projecting images with myopic defocus on the periphery of the retina of a wearer.

FIG. 2B shows a soft contact lens 10 comprising a plurality of light sources and optics and associated circuitry, in accordance with some embodiments. The contact lens 10 comprises a plurality of projection units 18. Each of the plurality of projection units 18 comprises a light source and one or more optics to focus light in front of the retina as described herein. Each of the optics may comprise one or more of a mirror, a plurality of mirrors, a lens, a plurality of lenses, a diffractive optic, a Fresnel lens, a light pipe or a wave guide. The contact lens 10 may comprise a battery 20 and a sensor 22. The contact lens 10 may comprise a flex printed circuit board (PCB) 24, and a processor can be mounted on the PCB 24. The processor can be mounted on the PCB 24 and coupled to the sensor 22 and the plurality of light sources 30. The soft contact lens 10 may also comprise wireless communication circuitry and an antenna for inductively charging the contact lens 10. Although reference is made to a battery 20, the contact lens 10 may comprise any suitable energy storage device. The soft contact lens 10 may comprise a lens body composed of any suitable material such as a hydrogel. The hydrogel can encapsulate the components of the soft contact lens 10.

The processor can be configured with instructions to illuminate the retina with the plurality of light sources 30. The processor can be programmed in many ways, for example with instructions received with the wireless communication circuitry. The processor can receive instructions for a user mobile device.

The sensor 22 can be coupled to the processor to allow the user to control the contact lens 10. For example, the sensor 22 can be configured to respond to pressure, such as pressure from an eyelid. The processor can be coupled to the sensor 22 to detect user commands.

The electronic control system may comprise a processor such as an ASIC or a microcontroller, a rechargeable Lithium ion solid state battery, a voltage ramping module e.g., a buck boost converter, a flash memory and an EEPROM, an RFID module to provide wireless recharging, or an antenna preferably disposed radially near an edge of the contact lens 10, and any combination thereof. The contact lens 10 may comprise a biocompatible material, such as a soft hydrogel or silicone hydrogel material, and may comprise any material composition that has proven to be compatible with sustained wear on the eye 11 as a contact lens 10.

FIG. 2C shows mechanical integration of the function of the components of the contact lens 10 as in FIG. 2B. These components can be supported with the PCB 24. For example, the power source such as a battery 20 can be mounted on the PCB 24 and coupled to other components to provide a power source function 21. The sensor 22 can be configured to provide an activation function 23. The sensor 22 can be coupled to a processor mounted on the PCB 24 to provide a control function 25 of the contact lens 10. The control function 25 may comprise a light intensity setting 27 and a light switch 29. The processor can be configured to detect signal from the sensor 22 corresponding to an increase in intensity, a decrease in intensity, or an on/off signal from the sensor 22, for example with a coded sequence of signals from the sensor 22. The processor is coupled to the light projection units 18 which can comprise a light source 30 and optics 32 to provide the projection function 31. For example, the processor can be coupled to the plurality of light sources 30 to control each of the light sources 30 in response to user input to the sensor 22.

In some embodiments, the optic configuration 32 comprises a plurality of mirrors configured to collect light emitted by the micro-displays 12, then direct the light beam to the pupil of the eye 11, in order to form an eccentric retinal image, as shown in FIGS. 3 and 4. The mirrors may collimate the light beam, or direct the light beam toward the retina 33 with a suitable vergence so as to focus the light beam onto the retina 33.

The specifications of the optical configuration are shown in Table 1.

TABLE 1 Basic optic parameters of the optic configuration shown in FIG. 3. Value (Reflective Value (Single Lens Characteristics Design) Design) Size of the light source 10 microns 10 microns Diameter of the optic 1.1 mm 0.292 mm Decentration of the light 1.75 mm 1.75 mm source from the center of the contact lens Wavelength 507 nm 507 nm Thickness of optic 300 microns 250 microns Retinal image location 27 degrees 27 degrees eccentric eccentric Size of the retinal image 200 microns 1100 microns

A comparison of the simulated image size for the optic configuration shown in FIG. 3 and the retinal resolution at 27 degrees eccentricity shows that the peripheral retina 33 at this eccentricity will be able to perceive this image.

In some embodiments, three performance attributes of the optic configuration include one or more of:

1. Image magnification, controlling image resolution,

2. Depth of focus, controlled by the optical path length of the optic configuration, and

3. Diffraction, as measured by the Airy Diameter.

The mirror assembly shown in FIG. 3 achieves a depth of focus that is less than 1 D, enabling the applied defocus of 2.0-4.0 D to be clearly perceived by the peripheral retina 33 at the specified eccentricity (20-30 degrees).

In some embodiments, the spots size of the image focused in front of the retina 33 comprises a resolution finer than the resolution of the retina 33. Retinal resolution generally decreases as a function of eccentricity. For example, at an angle of 0 degrees of eccentricity, retinal resolution is approximately 10 micrometers. At 5 degrees of eccentricity, the retinal resolution is approximately 30 micrometers. At 20 degrees of eccentricity, the resolution is approximately 100 micrometers and at 30 degrees the retinal resolution is approximately 150 micrometers.

FIGS. 5A and 5B show analysis of retinal image quality generated by the optic configuration of FIG. 3. Images formed by three of the four light sources 30 have been simulated. The temporal point has been omitted because it is symmetrical to the nasal point. The analysis shows that the image quality exceeds the resolving power of the retina 33 at 27 degrees eccentricity. The modulation transfer function of the retinal image created by the mirror assembly of FIG. 3 is diffraction limited, indicating that aberrations of the optical elements deployed are not causing significant deterioration of image quality, in accordance with this embodiment. Furthermore, the spatial resolution of the optics exceeds the resolution of the retina 33 at the preferred image location.

FIG. 6 shows analysis of depth of focus of the optic configuration shown in FIG. 3. Each millimeter of distance from the retina 33 represents a defocus of 2.7 D. This analysis shows that the depth of focus is sufficiently small that a defocus of 0.5 mm (1.35 D) is perceivable by the retina 33 at the point of incidence of the image (27 degrees eccentricity). Depth of focus depends on effective path length of the stimulating beam.

FIG. 7 shows the plot of MTF values against defocus shows the depth of focus of image created by each of the light sources (object).

A second embodiment comprises optics 32 comprising a converging or collimating lens in optical coupling with light source 30, as shown in FIGS. 8A and 8B. In this configuration a lens 34, which may comprise a single lens, is used to collimate the light output from the stimulation source and direct it to the cornea 37 through the contact lens 10. The effectiveness of the collimating lens 34 depends on its refractive index and should be sufficiently high in order to create a substantial difference in refractive indices between the lens material and the material of the contact lens 10 that functions as the substrate. In this example, the refractive index of the embedded lens 34 has been assumed to be 2.02 (e.g., refractive index of a lanthanum fluorosilicate glass LaSF₅), although other materials may be used.

Optical performance of the embodiment of FIGS. 8A and 8B is shown in FIGS. 9 and 10. Images formed by three of the four light sources 30 have been simulated. The temporal point has been omitted because it is symmetrical to the nasal point. Each millimeter of distance from the retina 33 represents a defocus of 2.7 D. This analysis shows that the depth of focus is substantially higher than 1 D, so that image blur caused by a defocus of 0.5 mm (1.35 D) may not be perceivable by the retina 33 at the point of incidence of the image (27 degrees eccentricity).

The analysis shows that the image quality exceeds the resolving power of the retina 33 at 27 degrees eccentricity. The optical path length of the single lens design is much shorter in this case, therefore, image magnification is substantially higher (110×, as opposed to 20× for the reflective design.). The spatial frequency resolution at 50% contrast (Modulus of OTF) is lower, approximately 15 line pairs per millimeter (“lp/mm”), compared with 50 lp/mm for the reflective design. Depth of focus has been estimated for this embodiment, again using Liu Brennan eye model to simulate the ocular optics, including ocular aberrations, as shown in FIG. 10. The depth of focus is greater than 1.0 D, indicating that changes in image resolution as a function of defocus may not be easily perceivable by the peripheral retina 33, especially since the resolution capability of the retina 33 at that eccentricity (20-30 degrees), derived mainly from rods is relatively poor as described herein.

A third embodiment comprises a light-pipe 36 in order to increase the optical path length, as shown in FIGS. 11A and 11B. The light-pipe 36 can provide an increased optical path length to decrease image magnification and retinal image size. However, depth of focus is relatively large, and the resolution is relatively coarse (15 lp/mm at 50% MTF).

Numerous other optical configurations may be considered, including the use of a micro-lens array with a point source, use of diffractive optics in order to use a thinner lens, generation of multiple retinal images using a single point source and an optical processing unit. In all case, the three characteristics listed above may be used as metrics in order to evaluate the suitability of a particular design.

Each embodiment disclosed herein can be combined with any one or more of the other embodiments disclosed herein, and a person of ordinary skill in the art will recognize many such combinations as being within the scope of the present disclosure.

The presently disclosed methods and apparatus are well suited for combination with many types of lenses, such as one or more of: smart contact lenses, contact lenses with antennas and sensors, contact lenses with integrated pulse oximeters, contact lenses with phase map displays, electro-optic contact lenses, contact lenses with flexible conductors, autonomous eye tracking contact lenses, electrochromic contact lenses, dynamic diffractive liquid crystal lenses, automatic accommodation lenses, image display lenses with programmable phase maps, lenses with tear activated micro batteries, tear film sensing contact lenses, lenses with multi-colored LED arrays, contact lenses with capacitive sensing, lenses to detect overlap of an ophthalmic device by an eyelid, lenses with active accommodation, lenses with electrochemical sensors, lenses with enzymes and sensors, lenses including dynamic visual field modulation, lenses for measuring pyruvate, lenses for measuring urea, lenses for measuring glucose, lenses with tear fluid conductivity sensors, lenses with near eye displays with phase maps, or lenses with electrochemical sensor chips.

A soft contact lens 10 is shown in FIG. 12. This contact lens 10 comprises a base or carrier contact lens comprising embedded electronics and optics. The base soft contact lens 10 is made of a biocompatible material such as a hydrogel or a silicone hydrogel polymer designed to be comfortable for sustained wear. In some embodiments, the contact lens 10 has a central optical zone 14 of diameter within a range from 6 mm to 9 mm, for example within a range from 7.0 mm to 8.0 mm. The central optical zone 14 is circumscribed by an outer annular zone, such as a peripheral zone 16 of width in a range 2.5 mm to 3.0 mm. The outer annular zone is surrounded by an outermost edge zone 18 of width in the range from 0.5 mm to 1.0 mm. The optical zone 14 is configured to provide refractive correction and can be spherical, toric or multifocal in design, for example. The outer annular zone peripheral to the optical zone 14 is configured to fit the corneal curvature and may comprise rotational stabilization zones for translational and rotational stability, while allowing movement of the contact lens 10 on the eye 11 following blinks. The edge zone 18 may comprise a thickness within a range from 0.05 mm to 0.15 mm and may end in a wedge shape. The overall diameter of the soft contact lens 10 can be within a range from 12.5 mm to 15.0 mm, for example within a range from 13.5 mm to 14.8 mm.

The embedded light sources 30 and the electronics are preferably located in the outer annular zone of the contact lens 10, as shown in FIG. 12. The central optical zone 14 is preferably free from electronics and light sources 30 in order to not compromise the quality of central foveal or macular vision, in accordance with some embodiments. In some embodiments, the edge zone 18 does not comprise circuitry in order to maintain contact with the corneal surface and provide comfort.

The light sources can be arranged in many ways on the contact lens. For example, the light sources can be arranged in a substantially continuous ring around the central optical zone. In some embodiments, the plurality of light sources and the plurality of optics (e.g., lenses, mirrors or light guides) are coupled together to form a continuous ring of illumination.

The contact lens 10 of FIG. 12 comprises of a body composed of a soft biocompatible polymer with high oxygen permeability embedded with a transparent film populated with all the electronic and optical components. This transparent film may comprise a transparent printed circuit board (“PCB”) substrate. The thickness of the PCB can be within a range from about 5 microns to 50 microns and may comprise a plurality of layers of the film in order to utilize both surfaces of the PCB substrate for population of electronics. The PCB substrate can be curved to conform to the geometry of the base contact lens 10, with a curvature within a range about 7.5 mm to about 10.0 mm, for example within a range from about 8.0 mm to about 9.5 mm, for example. The PCB substrate can be configured for suitable oxygen permeability. In some embodiments, the PCB is perforated to improve permeability of oxygen, tear fluid, nutrients and carbon dioxide through it. In some embodiments, the PCB has a low tensile modulus, for example within a range from about 1 MPa to about 50 MPa, although stiffer films may also be used for example. In some embodiments, a preferred material for a transparent flexible PCB substrate comprises a polyimide that is cast from a liquid or a solution, and may be in the form of a polyamic acid when spin cast on a flat substrate, subsequently cured thermally to form a polyimide such as Kapton™.

The contact lens 10 may comprise one or more components shown in FIG. 12. The architecture of the electronic system, shown in FIG. 12 comprises a plurality of light sources 30 mounted on a bus, a microcontroller 38 that comprises a power and data management system, an onboard memory and an RFID module, a sensor that is designed to detect a physical or physiological trigger and issue a signal that turns the light sources 30 ON or OFF, an antenna 41 for wireless exchange of data that also functions as a wireless receiver of power, operating on a single or multiple frequency bands for transmission of data and power and a rechargeable solid state Lithium ion battery 20. In some embodiments, the microcontroller 38 comprises an application specific integrated circuitry (“ASIC”). The plurality of light sources 30 may comprise microscopic light sources 30 as described herein.

The light sources 30 can be positioned along a circumference of diameter in the range 1.5 mm to 5.0 mm from the center.

FIG. 13 shows a ray tracing analysis of the image of a light source 30 formed on an outer region of the retina 33 such as the peripheral retina 33. In this simulation, the anterior chamber depth is assumed to be 4.1 mm, typically between 2.9 mm and 5.0 mm for human subjects, the axial length has been assumed to be 25.0 mm, and the contact lens 10 is positioned on the cornea. The microscopic light source 30 is placed 1.9 mm away from the center of the contact lens 10, leaving a central optical zone 14 of 3.8 mm in diameter that is clear.

Referring again to FIGS. 12 and 13, a combination of a light source 30 and a lens such as a micro-lens can be used to direct light to an outer region of the retina 33. The micro-lens can be configured to collect light emitted by the light source 30. The collected light can be one or more of collimated or focused and directed to the pupil of the eye 11. In some embodiments, a projection system comprises the combination of the microlight source 30 and the image forming optics 32.

The light source 30 may comprise one or more of an organic light emitting diode (OLED), a quantum dot light emitting diode (QLED), a transparent light emitting diode (TOLED), an inorganic light emitting diode (i-LED) or a CRT display. The light source 30 may comprise one or more pixels, populated on a transparent or opaque substrate. The light source 30 may comprise one or more display components such as a passive matrix or an active matrix, for example. In some embodiments, a size of individual pixels is within a range from 1 to 10 microns, for example within a range from 2 to 5 microns. The brightness of each of the plurality of pixels when turned ON can be more than 500 nits (Cd/m²), more than 5000 nits, or within a range from 10,000 to 25,000 nits.

The resolving power of the retina 33 is highest at the center, the fovea. Healthy young persons are capable of angular resolution of 0.6 arc minute, equivalent to 20/12 in Snellen terminology. Resolution capability is typically reduced to 20/200 (10 arc minute) at 25 degrees eccentricity. There are few if any cones at this eccentricity, and the population of rods is also much diminished.

In some embodiments, the image delivery system provides an image resolution equal or exceeding the level of retinal image resolution. In some embodiments, there is no additional benefit can be expected if the projected image resolution exceeds the resolution capability of the retina 33 at the location of the image. In some embodiments, the spot size of the image at the retinal periphery is therefore 150 microns or less.

The wavelengths of light emitted by the light source 30 can be configured in many ways. The wavelength of light emitted by the light source 30 can be determined by clinical studies in accordance with the present disclosure. In some embodiments, the wavelength of the light source 30 comprises light that corresponds to the peak sensitivity of retinal photoreceptors at the desired eccentricity, e.g. substantially matches the peak sensitivity. In some embodiments light is projected at an eccentricity of 20-30 degrees where rods are predominant, and the light from the source comprises wavelengths within a range from about from about 420 nm to 600 nm, for example from about 490 nm to 530 nm, for example within a range from about 500 to 520 nm, for example from about 502 to 512 nm. In some of the wavelength simulations disclosed herein 507 nm light is used as the input wavelength parameter. The optical designs disclosed herein are applicable to all wavelengths, even though the precise results of optimized design parameters may change with wavelength, due to chromatic dispersion of the material comprising the projection unit.

Work in relation to the present disclosure suggest that two design constraints may influence the selection of design input parameters in some of the embodiments that follow. These are:

1. Dimensions of the projection unit 18, so that they can be embedded into the contact lens 10 without the lens thickness being too high. In some embodiments, the maximum lens thickness in the outer annular zone is 400 microns, which is consistent with current soft contact lenses for refractive corrections.

2. Optical path length between the microscopic light source 30 and the image forming system. This is related to control of image magnification and magnitude of image blur caused by diffraction, which can be quantified as the Airy Disk diameter. Image magnification is given by the ratio of the focal length of the image projection unit to the focal length of the eye 11, which is generally assumed to be 17 mm for first order estimates. In some embodiments, it is specific to the individual eye. In some embodiments, the Airy disk diameter, (2.44×λ (in microns)×f/≠) is no more than the retinal resolution limit at image location. For example, the minimum spot size at eccentricity of 25 degrees is 150 microns, so the Airy Disk diameter should not exceed 150 microns and can be less than 150 microns. Since the focal length of the eye 11 is fixed, the aperture of the projection optic controls the Airy Disk diameter at any wavelength.

In some embodiments, size of the Airy Disk of the collection optics and light sources 30 and associated image as described herein is related to the retinal image resolution. For example, at 30 degrees, 25 degrees, 20 degrees, 15 degrees and 10 degrees, the Airy Disk size may be no more than about 150 micro-meters (“microns”, “um”) about 125 um, about 100 um, about 75 um, and about 60 um, respectively.

The image forming system can be configured in many ways including without limitation, diffractive optical elements, Fresnel lenses, refractive optics or reflective optics.

The following simulations provide optical results in accordance with some embodiments disclosed herein.

TABLE 2 Input parameters of the second optical simulations. Optical Component or property Value Size of Light Source 10 microns Max Thickness of the light projection unit 300 microns Image location on the retinal periphery 27° eccentric to the fovea Diameter of the projection unit 1.1 mm Optic design Aspheric 8^(th) order, 4^(th) order Zernike polynomials Offset between the center of the contact 1.75 mm lens and the light projection unit Wavelength of Light 507 nm

In some embodiments, the area covered by the overall image is preferably an arcuate segment of 5-10 degrees by 30-45 degrees, or 150-450 degree² for every light source, or about 3.0-6.0 mm² in area. In some embodiments, four such light sources 30 at each quadrant of the contact lens 10 deliver four such peripheral images for optimum neurostimulation to the retina 33. An embodiment in accordance with the second simulations of the image delivery system is shown in FIG. 3. In this embodiment, a system of convex 26 and concave 28 micro-mirrors is used to increase optical path length and thereby image magnification of the peripheral retinal image. FIG. 4 shows the light path of the peripheral image through the eye 11 for this embodiment. An exemplary light source 30 can be defined, assuming that the diameter of the light source 30 is 10 μm, and thickness is 100 μm. Four object points 40 can be specified to simulate the image quality, as shown in FIG. 14. With reference to FIG. 14, the simulated light source 30 is shown with the dashed circle of 10 μm and the simulated object points 40 includes the smaller circles and the center points of each of the smaller circles. Table 2 shows the input parameters of the simulation.

Output of the simulation are: Image magnification and size, Image quality and Depth of focus. The same input and output parameters were used to simulate all the preferred embodiments. Image size of the first preferred embodiment was found to be 200 microns, image magnification being 20×. Results of simulation of image quality is shown in FIG. 15 for this simulation. All MTF plots are virtually coincident. The MTF plots indicate that the resolution of the peripheral image is substantially better than the limits of retinal resolution at this eccentricity.

The depth of focus of the peripheral image was also simulated for the reflective optic in the second simulations and is shown in FIG. 16. In some embodiments, the image is optimally formed at a distance of 2.0 mm in front of the retina 33, causing it to be myopically defocused on the retina 33. In some embodiments, the blur induced by this myopic defocus overcomes the effect of depth of focus, so that the retina 33 perceives a blurred image for it to perceive a neurostimulation to move forward, reducing the axial length of the eye 11. In some embodiments, the neural stimulation is sufficient to decrease axial growth of the eye 11.

FIG. 17 shows the effect of image blur caused by myopic defocus in the form of loss of contrast or the modulus of simulated MTF plots shown for a particular spatial frequency (20/200 or 10 arc minutes) for the second simulations. The increase in spot size shown in FIG. 16 is reflected in and consistent with the loss of the magnitude of the MTF plots as a function of the magnitude of myopic defocus. The second simulations indicate that the focal length of the projection unit is 0.85 mm with an image size 200 microns and an image magnification is 20×. The Airy disk diameter is computed to be 8.9 microns, while the Raleigh criterion is 10.9 microns.

Referring again FIGS. 10A and 1 which show a lens to collect light from the light source 30 and direct light toward the retina 33, and the path of light along the eye 11, respectively. In some embodiments, the light source 30 faces a refractive lens that approximately collimates the light which is finally projected in front of the peripheral retina 33, creating a myopic defocus of the peripheral image. Although reference is made to a refractive lens, other lenses can be used such as diffractive optics and gradient index (GRIN) lenses. Table 3 shows the design parameters of the refractive lens used for the third simulations of the peripheral image.

TABLE 3 Design input parameters of the third simulations. Lens Parameters Value Diameter of the light source 10 microns Wavelength used for simulation 507 nm Diameter of the optic 292 microns Thickness of the optic 250 microns Refractive index of the micro-lens 2.2 Image location on the retina 27 degrees eccentric Thickness of the projection optic 350 microns Distance of light source from center of contact lens 1.75 mm Collimating lens design 14^(th) order aspheric

The results of these simulations show that the image size is 1100 microns with an image magnification of 110. The MTF plots are shown in FIG. 18 for the four object points 40 shown in FIG. 14. The magnitude of MTF plots at high spatial frequencies are substantially lower than those for the reflective optic. The MTF plots show that image resolution is adequate for image of eccentricity 27 degrees. The optical design of the second preferred embodiment leads to a much greater depth of focus, as shown in FIG. 19. This means that in some embodiments the effective image blur is much less for a myopic defocus in the range of 2D to 5 D, relative to the reflective optic, in accordance with the first and second simulations. The increased depth of focus is reflected in the MTF plots shown in FIG. 20, which may have a lesser dependence on the magnitude of myopic defocus relative to the reflective optic configuration, shown in FIGS. 3 and 4.

The third optical simulations show that the refractive optic may successfully project a peripheral retinal image with an acceptable image size and image magnification and depth of focus. Although the image size, magnification and depth of focus may be somewhat larger than for the reflective configuration of the second simulations.

Although MTF values at high spatial frequencies (50 lp/mm and above) are lower for this refractive optic design than the reflective design, image quality at high spatial frequencies can be somewhat is less relevant at the peripheral locations of the retinal image due to decreased visual acuity. The third simulations show that the focal length of the projection unit is 0.15 mm with an image size of 1100 microns and an image magnification is 110×. The Airy disk diameter is computed to be 36.7 microns, while the Raleigh criterion is 44.8 microns.

Referring again to FIGS. 11A and 11B, which shows a light guide, fourth simulations were conducted for this configuration comprising a light guide, a mirror and a lens. In the simulated embodiments, the focusing lens is located at the end (exit aperture) of the light pipe. In some embodiments, the light pipe comprises a curved lens surface on the end to focus light. In this lightguide embodiment, the projection optic comprises a light guide comprising a mirror and a lens.

In some embodiments, the light source 30 is placed in an outer portion of the contact lens 10, e.g. near the periphery, and light from the source is guided to a mirror that collects the light and deflects the light towards the eye 11 to generate an image in front of the peripheral retina 33 with a myopic defocus as described herein. In some embodiments, the function of the light guide is to increase the length of the light path, so as to reduce image magnification and increase resolution of the image formed anterior to the retina 33.

TABLE 4 Lens parameters used as inputs to the fourth simulations. Optics Property or Parameter Value Diameter of source 10 microns Wavelength of simulation 510 nm Length of Light Guide 2.7 mm Refractive index of material of 2.2 projection optics Diameter of mirror 400 microns Decenter of optic relative to center 1.75 mm of contact lens Thickness of optic 290 microns Image location 25 degrees eccentric to fovea Optical design and Image simulation Aspheric 6^(th) order, Zernike 3^(rd) order

Table 4 gives the properties of the projection system used in the fourth simulations of peripheral retinal image quality formed by light guide embodiments. Image magnification was 14 with an image size of 140 microns. These simulations reveal that the image magnification is acceptable, the depth of focus is not as large as the refractive optic, but larger than the reflective optic. The fourth simulations indicate that the focal length of the projection unit is 1.21 mm with an image size of 140 microns and a magnification of 14X. The Airy disk diameter is computed to be 34.8 microns, while the Raleigh criterion is 42.6 microns.

The three results of the second, third and fourth simulations for the three corresponding configurations were compared with one another in terms of their size, the depth of focus produced by each defining a sharpness gradient of the defocused image as a function of magnitude of myopic defocus, and the beam diameter. The results show that the second simulations comprising the reflective optic has the best sharpness gradient, while the embodiment comprising the refractive optic has the smallest sharpness gradient, with the lightguide based projection unit providing a limited sharpness gradient, as shown in FIG. 24. Each of these approaches can be configured to decrease axial length growth in accordance with the teachings disclosed herein.

The three embodiments also differ considerably in terms of the diameter of the optic, as shown in table 5.

TABLE 5 Optic diameters used in the three simulations. Configuration Optic Diameter Reflective optic 1.1 mm Refractive optic 0.3 mm Lightguide optic 0.4 mm

The reflective optic and light source 30 can be configured in many ways, and additional simulations can be conducted to determine appropriate configurations in accordance with the teachings disclosed herein. For example, clarity at the central object point shown in FIG. 14 can be disregarded because its contribution to the neurostimulation is likely to be limited. Such simulations and optimizations can allow a reduction of the diameter of the projection unit and its thickness, which can be helpful when the system is embedded into a contact lens 10 that provides a high level of comfort to wearers as described herein. The design input parameters for a fifth simulation are shown in Table 6. The results show that the image magnification can be increased to 25, providing an image size of 250 microns for a 10 micron source, which is acceptable for a peripheral image anterior to the retina 33 in accordance with the embodiments disclosed herein. The output of these fourth image simulations is shown in FIGS. 25 and 26. The sharpness gradient, that is the variation of image spot size or MTF at a single spatial frequency as a function of magnitude of myopic defocus are still quite acceptable while providing a decreased size of the projection system.

As detailed herein, the computing devices and systems described and/or illustrated herein broadly represent any type or form of computing device or system capable of executing computer-readable instructions, such as those contained within the modules described herein. In their most basic configuration, these computing device(s) may each comprise at least one memory device and at least one physical processor.

The term “memory” or “memory device,” as used herein, generally represents any type or form of volatile or non-volatile storage device or medium capable of storing data and/or computer-readable instructions. In one example, a memory device may store, load, and/or maintain one or more of the modules described herein. Examples of memory devices comprise, without limitation, Random Access Memory (RAM), Read Only Memory (ROM), flash memory, Hard Disk Drives (HDDs), Solid-State Drives (SSDs), optical disk drives, caches, variations or combinations of one or more of the same, or any other suitable storage memory.

In addition, the term “processor” or “physical processor,” as used herein, generally refers to any type or form of hardware-implemented processing unit capable of interpreting and/or executing computer-readable instructions. In one example, a physical processor may access and/or modify one or more modules stored in the above-described memory device. Examples of physical processors comprise, without limitation, microprocessors, microcontrollers, Central Processing Units (CPUs), Field-Programmable Gate Arrays (FPGAs) that implement softcore processors, Application-Specific Integrated Circuits (ASICs), portions of one or more of the same, variations or combinations of one or more of the same, or any other suitable physical processor.

Although illustrated as separate elements, the method steps described and/or illustrated herein may represent portions of a single application. In addition, in some embodiments one or more of these steps may represent or correspond to one or more software applications or programs that, when executed by a computing device, may cause the computing device to perform one or more tasks, such as the method step.

In addition, one or more of the devices described herein may transform data, physical devices, and/or representations of physical devices from one form to another. For example, one or more of the devices recited herein may receive image data of a sample to be transformed, transform the image data, output a result of the transformation to determine a 3D process, use the result of the transformation to perform the 3D process, and store the result of the transformation to produce an output image of the sample. Additionally or alternatively, one or more of the modules recited herein may transform a processor, volatile memory, non-volatile memory, and/or any other portion of a physical computing device from one form of computing device to another form of computing device by executing on the computing device, storing data on the computing device, and/or otherwise interacting with the computing device.

The term “computer-readable medium,” as used herein, generally refers to any form of device, carrier, or medium capable of storing or carrying computer-readable instructions. Examples of computer-readable media comprise, without limitation, transmission-type media, such as carrier waves, and non-transitory-type media, such as magnetic-storage media (e.g., hard disk drives, tape drives, and floppy disks), optical storage media (e.g., Compact Disks (CDs), Digital Video Disks (DVDs), and BLU-RAY disks), electronic-storage media (e.g., solid-state drives and flash media), and other distribution systems.

A person of ordinary skill in the art will recognize that any process or method disclosed herein can be modified in many ways. The process parameters and sequence of the steps described and/or illustrated herein are given by way of example only and can be varied as desired. For example, while the steps illustrated and/or described herein may be shown or discussed in a particular order, these steps do not necessarily need to be performed in the order illustrated or discussed.

The various exemplary methods described and/or illustrated herein may also omit one or more of the steps described or illustrated herein or comprise additional steps in addition to those disclosed. Further, a step of any method as disclosed herein can be combined with any one or more steps of any other method as disclosed herein.

Unless otherwise noted, the terms “connected to” and “coupled to” (and their derivatives), as used in the specification and claims, are to be construed as permitting both direct and indirect (i.e., via other elements or components) connection. In addition, the terms “a” or “an,” as used in the specification and claims, are to be construed as meaning “at least one of.” Finally, for ease of use, the terms “including” and “having” (and their derivatives), as used in the specification and claims, are interchangeable with and shall have the same meaning as the word “comprising.

The processor as disclosed herein can be configured with instructions to perform any one or more steps of any method as disclosed herein.

It will be understood that although the terms “first,” “second,” “third”, etc. may be used herein to describe various layers, elements, components, regions or sections without referring to any particular order or sequence of events. These terms are merely used to distinguish one layer, element, component, region or section from another layer, element, component, region or section. A first layer, element, component, region or section as described herein could be referred to as a second layer, element, component, region or section without departing from the teachings of the present disclosure.

As used herein, the term “or” is used inclusively to refer items in the alternative and in combination.

Each embodiment disclosed herein can be combined with any one or more of the other embodiments disclosed herein, and a person of ordinary skill in the art will recognize many such combinations as being within the scope of the present disclosure.

The present disclosure includes the following numbered clauses:

Clause 1. An electronic contact lens to treat myopia of an eye having a retina, comprising:

a plurality of light sources; and a plurality of projection optics coupled to the plurality of light sources to project a plurality of images anterior to the retina decrease a progression of myopia of the eye.

Clause 2. The electronic contact lens of clause 1, wherein said lens is configured to reverse myopia.

Clause 3. The electronic contact lens of clause 1, wherein said plurality of projection optics is arranged to project the plurality of images of the plurality of light sources at a plurality of outer regions of the retina of the eye with an eccentricity within a range from 15 degrees to 30 degrees with respect to a fovea of the eye.

Clause 4. The electronic contact lens of clause 1, wherein each of said plurality of projection optics is arranged to project an image myopically defocused with respect to a retinal surface, wherein an amount of said defocus is within a range from 2.0 D to 5.0 D.

Clause 5. The electronic contact lens of clause 1, wherein each of said plurality of projection optics is located 1.5 mm to 5.0 mm from a center of said contact lens and optionally wherein the plurality of projection optics is located along the circumference of a circle.

Clause 6. The electronic contact lens of clause 1, wherein said plurality of projection optics comprises a plurality of image forming optics optically coupled to said plurality of light sources to project the plurality of images anterior to the surface of the retina.

Clause 7. The electronic contact lens of clause 6, wherein each of said plurality of light sources has a maximum distance across not exceeding 26 microns and optionally no more than 10 microns and optionally wherein said maximum distance across comprises a diameter.

Clause 8. The electronic contact lens of clause 6, wherein each of the plurality of projection optics comprises one or more of a mirror, a lens, or a lightguide.

Clause 9. The electronic contact lens of claim 8, wherein each of the plurality of image forming optics comprising one or more of a diffractive element, a Fresnel lens, or a compound Gabor lens.

Clause 10. The electronic contact lens of clause 8, wherein each of the plurality of image forming optic has a maximum distance across within a range from 1.5 mm to 200 microns and optionally wherein said maximum distance across comprises a diameter.

Clause 11. The electronic contact lens of clause 8, wherein each of the plurality of image forming optics is aspheric and corrected for image aberrations.

Clause 12. The electronic contact lens of clause 8, wherein each of the plurality of image forming optics comprises a combination of convex and concave mirrors.

Clause 13. The electronic contact lens of clause 11, wherein said each of the plurality of image forming optic forms an image anterior to an outer portion of the retina at an eccentricity within a range from 15 degrees to 30 degrees from a fovea and optionally within a range from 25 degrees to 30 degrees from the fovea.

Clause 14. The electronic contact lens of clause 11, wherein said each of the plurality of image forming optics creates an image anterior to the retina with an image of magnification within a range from 25 to 100.

Clause 15. The electronic contact lens of clause 1, wherein the image anterior to the outer portion of the retina comprises magnitude of modulation transfer function of no less than 0.75 at a spatial frequency of 10 lp/mm, and no less than 0.40 at a spatial frequency of 50 lp/mm.

Clause 16. The electronic contact lens of clause 8, wherein each of the plurality of projection optics comprises an image forming optic comprising a collimating optic configured to form the image anterior to the retina.

Clause 17. The electronic contact lens of clause 8, wherein said projection optic comprises a single lens to function both as a collimating optic and an image forming optic.

Clause 18. The electronic contact lens of clause 8, wherein said projection optic comprises an image forming optic to create an image anterior to an outer portion of the retina with eccentricity no more than 30 degrees and a depth of focus of no more than 1.0 D.

Clause 19. The electronic contact lens of clause 17, wherein said optic creates the image anterior to an outer portion of the retain with an eccentricity no more than 30 degrees, wherein a modulation transfer function of said image decreases by a minimum of 0.1 units for a defocus of 1.0 diopters.

Clause 20. A soft contact lens comprising:

a plurality of light sources coupled to a plurality of optical elements, the plurality of light sources and the plurality of optical elements embedded in a soft contact lens material, wherein each of said plurality of optical elements generates an image focused in front of a peripheral retina of a wearer.

Clause 21. The soft contact lens of clause 20, wherein the plurality of light sources comprises a plurality of micro-displays.

Clause 22. The soft contact lens of clause 20, wherein the plurality of light sources comprises a plurality of light emitting diodes (LEDs).

Clause 23. The soft contact lens of clause 20, wherein each of said plurality of optical elements comprises a mirror assembly that collimates light emitted by a corresponding micro-display and directs a resulting light beam into the pupil of the eye, wherein said light beam is focused to form the peripheral image in front of the retina.

Clause 24. The soft contact lens of clause 20, wherein each of said plurality of optical elements comprise a lens that receives light emitted by a corresponding microdisplay and directs a resulting light beam into the pupil of the eye, wherein said light beam is focused to form an image in front of the retina.

Clause 25. The soft contact lens of clause 20, wherein said the plurality of light sources generates a polychromatic illumination and optionally wherein the plurality of light sources comprises a plurality of micro-displays generating polychromatic illumination.

Clause 26. The soft contact lens of clause 20, wherein said image is about 0.5 mm to 2.0 mm in front of the retina.

Clause 27. The soft contact lens of clause 20, wherein said image has a resolution of at least 30 lp/mm.

Clause 28. The soft contact lens of clause 20, wherein said image has a magnification of no more than 100×.

Clause 29. The soft contact lens of clause 20, wherein said image has a depth of focus no more than 2.5 diopters and optionally wherein said depth of focus is no more than about 0.9 mm.

Clause 30. The soft contact lens of clause 20, wherein said image is projected at an eccentricity in the within a range from about 15 degrees to about 45 degrees.

Clause 31. The soft contact lens of clause 30, wherein said range is from about 25 degrees to about 30 degrees.

Clause 32. The soft contact lens of clause 20, wherein said micro-display illuminates the pupil with an illuminance within a range from about 0.1 cd/m² to 10 cd/m².

Clause 33. The soft contact lens of clause 20, wherein the image is focused at a distance in front of the peripheral retina at a location and the image comprises a depth of focus and a spatial resolution, the depth of focus less than the distance, the spatial resolution greater than a spatial resolution of the peripheral retina at the location.

Clause 34. The soft contact lens of clause 20, further comprising a sensor to receive input from the wearer when the contact lens has been placed on an eye of the wearer.

Clause 35. The soft contact lens of any one of the preceding clauses, further comprising a processor coupled to the plurality of light sources to control illumination of the plurality of light sources.

Clause 36. The soft contact lens of any one of the preceding clauses, further comprising wireless communication circuitry operatively coupled to the plurality of light sources to control illumination of the plurality of light sources.

Clause 37. The soft contact lens of any one of the preceding clauses, further comprising wireless communication circuitry operatively coupled to a mobile device for the wearer to control illumination of the plurality of light sources.

Clause 38. The soft contact lens of any one of the preceding clauses, further comprising wireless communication circuitry operatively coupled to a processor for a health care provider to program illumination cycles and intensities of the plurality of light sources.

Clause 39. A soft contact lens embedded with at least one micro-display wherein said micro-display generates an image that is focused in front of the peripheral retina of a wearer.

Clause 40. The lens of clause 39, wherein said lens provides best refractive correction to refractive errors of the wearer.

Clause 41. The lens of clause 39, wherein said micro-display is displaced from the optical center of said lens by about 2.5 mm to about 5.0 mm.

Clause 42. The lens of clause 39, wherein it comprises a set of 4 to 8 microdisplays, disposed evenly along an arc of said lens, each being displaced equally from the optical center of said lens.

Clause 43. The lens of clause 39, wherein said image is focused 0.5 mm to 2.5 mm in front of the retina.

Clause 44. The lens of clause 39, wherein said image is focused 1.0 D to 3.0 D myopically relative to the best focus at the fovea of the wearer.

Clause 45. The lens of clause 39, wherein said lens comprises at least one microdisplay, an ASIC, a voltage ramp, a rechargeable battery, a wireless receiver and transmitter, a flash memory and a non-volatile memory.

Clause 46. The lens of clause 39, wherein said micro-display is a micro-OLED.

Clause 47. The lens of clause 39, wherein said micro-display is a micro-LED.

Clause 48. The lens of clause 39, wherein said micro-display is optically coupled with a micro-lens array.

Clause 49. The lens of any one of clauses 39 or 45, wherein said arrays have dimensions ranging from 1 mm² to 8 mm² and optionally from 1 mm² to 8 mm².

Clause 50. The lens of clause 39, wherein the duration of said image of clause 1 is programmable when the lens is on eye.

Clause 51. The lens of clause 47, wherein said image is projected continuously for about 1 hour to about 12 hours per day.

Clause 52. The lens of clause 47, wherein said image is projected episodically, several times a day, with the total duration of projection ranging from 1 hour to 12 hours per day.

Clause 53. The lens of clause 39, wherein said image is projected when the wearer is asleep.

Clause 54. The lens of clause 39, wherein said image is monochromatic, preferably at 500 nm.

Clause 55. The lens of clause 39, wherein said image is polychromatic, with a wavelength distribution that preferably matches the retinal response to visible light.

Clause 56. The lens of clause 39, wherein said lens is of daily disposable modality.

Clause 57. The lens of clause 39, wherein said lens is of planned replacement modality.

While preferred embodiments of the present invention have been shown and described herein, it will be obvious to those skilled in the art that such embodiments are provided by way of example only. It is not intended that the invention be limited by the specific examples provided within the specification. While the invention has been described with reference to the aforementioned specification, the descriptions and illustrations of the embodiments herein are not meant to be construed in a limiting sense. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the invention. Furthermore, it shall be understood that all aspects of the invention are not limited to the specific depictions, configurations or relative proportions set forth herein which depend upon a variety of conditions and variables. It should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention. It is therefore contemplated that the invention shall also cover any such alternatives, modifications, variations or equivalents. It is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby. 

What is claimed is:
 1. An apparatus to treat myopia of an eye having a retina, comprising: a lens; a plurality of light sources; and a plurality of projection optics coupled to the plurality of light sources to project a plurality of images anterior to the retina decrease a progression of myopia of the eye.
 2. The apparatus of claim 1, wherein said apparatus is configured to reverse myopia.
 3. The apparatus of claim 1, wherein said plurality of projection optics is arranged to project the plurality of images of the plurality of light sources at a plurality of outer regions of the retina of the eye with an eccentricity within a range from 15 degrees to 30 degrees with respect to a fovea of the eye.
 4. The apparatus of claim 1, wherein each of said plurality of projection optics is arranged to project an image myopically defocused with respect to a retinal surface, wherein an amount of said defocus is within a range from 2.0 D to 5.0 D.
 5. The apparatus of claim 1, wherein each of said plurality of projection optics is located 1.5 mm to 5.0 mm from a center of said contact lens and optionally wherein the plurality of projection optics is located along the circumference of a circle.
 6. The apparatus of claim 1, wherein said plurality of projection optics comprises a plurality of image forming optics optically coupled to said plurality of light sources to project the plurality of images anterior to the surface of the retina.
 7. The apparatus of claim 6, wherein each of said plurality of light sources has a maximum distance across not exceeding 26 microns and optionally no more than 10 microns and optionally wherein said maximum distance across comprises a diameter.
 8. The apparatus of claim 6, wherein each of the plurality of projection optics comprises one or more of a mirror, a lens, or a lightguide.
 9. The apparatus of claim 8, wherein each of the plurality of image forming optics comprising one or more of a diffractive element, a Fresnel lens, or a compound Gabor lens.
 10. The apparatus of claim 8, wherein each of the plurality of image forming optic has a maximum distance across within a range from 1.5 mm to 200 microns and optionally wherein said maximum distance across comprises a diameter.
 11. The apparatus of claim 8, wherein each of the plurality of image forming optics is aspheric and corrected for image aberrations.
 12. The apparatus of claim 8, wherein each of the plurality of image forming optics comprises a combination of convex and concave mirrors.
 13. The apparatus of claim 11, wherein said each of the plurality of image forming optic forms an image anterior to an outer portion of the retina at an eccentricity within a range from 15 degrees to 30 degrees from a fovea and optionally within a range from 25 degrees to 30 degrees from the fovea.
 14. The apparatus of claim 11, wherein said each of the plurality of image forming optics creates an image anterior to the retina with an image of magnification within a range from 25 to
 100. 15. The apparatus of claim 1, wherein the image anterior to the outer portion of the retina comprises magnitude of modulation transfer function of no less than 0.75 at a spatial frequency of 10 lp/mm, and no less than 0.40 at a spatial frequency of 50 lp/mm.
 16. The apparatus of claim 8, wherein each of the plurality of projection optics comprises an image forming optic comprising a collimating optic configured to form the image anterior to the retina.
 17. The apparatus of claim 8, wherein said projection optic comprises a single lens to function both as a collimating optic and an image forming optic.
 18. The apparatus of claim 8, wherein said projection optic comprises an image forming optic to create an image anterior to an outer portion of the retina with eccentricity no more than 30 degrees and a depth of focus of no more than 1.0 D.
 19. The apparatus of claim 17, wherein said optic creates the image anterior to an outer portion of the retina with an eccentricity no more than 30 degrees, wherein a modulation transfer function of said image decreases by a minimum of 0.1 units for a defocus of 1.0 diopters.
 20. The apparats of claim 1, wherein said plurality of light sources comprises from 4 to 8 micro-displays, disposed evenly along an arc of said lens, each being displaced equally from an optical center of said lens. 